Polysiloxane prepolymers for biomedical devices

ABSTRACT

A polysiloxane prepolymer that is useful for forming biomedical devices has the formula:
 
M(*Dii*PS) x *Dii*M  (I)
 
wherein:
         each M is independently a polymerizable ethylenically unsaturated radical;   each Dii is independently a diradical residue of a diisocyanate;   each PS is independently a diradical residue of a polysiloxane-diol or a polysiloxane-diamine;   each * is independently —NH—CO—NH—, —NH—COO— or —OCO—NH—; and   x is at least 2.

This application claims priority under 35 USC 119(e) of priorprovisional application Ser. No. 60/640,159, filed Dec. 29, 2004.

FIELD OF THE INVENTION

The present invention relates to polysiloxane prepolymers that areuseful for forming biomedical devices, particularly ophthalmic devicesincluding contact lenses, intraocular lenses and ophthalmic implants.This invention also relates to copolymers formed from the prepolymers,especially hydrogel copolymers.

BACKGROUND OF THE INVENTION

Hydrogels represent a desirable class of materials for the manufactureof various biomedical devices, including ophthalmic devices such ascontact lenses. A hydrogel is a hydrated cross-linked polymeric systemthat contains water in an equilibrium state. Hydrogel lenses offerdesirable biocompatibility and comfort. Silicone hydrogels are a knownclass of hydrogels and are characterized by the inclusion of asilicone-containing material. Typically, a silicone-containing monomeris copolymerized by free radical polymerization with a hydrophilicmonomer, with either the silicone-containing monomer or the hydrophilicmonomer functioning as a crosslinking agent (a crosslinker being definedas a monomer having multiple polymerizable functionalities) or aseparate crosslinker may be employed. An advantage of silicone hydrogelsover non-silicone hydrogels is that the silicone hydrogels typicallyhave higher oxygen permeability due to the inclusion of thesilicone-containing monomer.

Various polysiloxane-based prepolymers with urea or urethane linkageshave been disclosed as potential silicone-containing monomers forsilicone hydrogels. These various prepolymers may differ in theirmethods of preparation and in their physical characteristics/properties,and thus may exhibit divergent behavior when combined with othermonomers for hydrogel copolymers.

One class of urethane- or urea-containing polysiloxane prepolymersinvolves endcapping polysiloxane-diol or polysiloxane-diamine with anethylenically unsaturated monomer having an isocyanate group such asisocyanatoethyl methacrylate (IEM). For example, by reacting IEM withhydroxy-terminated polydimethylsiloxane, a prepolymer is formed. Ingeneral, this class of prepolymer exhibits similar compatibility withhydrophilic monomers as corresponding prepolymer without the urethanelinkage, especially for higher molecular weight prepolymers. Also, ingeneral, these prepolymers are liquid at room temperature. Examples ofsuch prepolymers are found in U.S. Pat. No. 4,605,712 (Mueller et al.).

A second class of urethane-containing polysiloxane prepolymers employs adiisocyanate to create urethane linkages. In general, these prepolymersare prepared by reacting 2 moles of diisocyanate with ahydroxy-terminated polydimethylsiloxane, followed by end capping with2-hydroxyethyl methacrylate (HEMA). This class exhibits slightimprovement in compatibility with hydrophilic monomers such asN,N-dimethylacrylamide (DMA), depending on the molecular weight ofpolysiloxane. Also, in general, it is a liquid at room temperature.Examples of such prepolymers are found in U.S. Pat. No. 4,136,250(Mueller et al.)

U.S. Pat. No. 5,034,461 (Lai et al.) discloses variouspolysiloxane-containing urethane or urea prepolymers. Generally, theseprepolymers are derived from a short chain diol, a hydroxy-terminatedpolydimethylsiloxane and a diisocyanate, such that the structuresresemble a segmented polyurethane elastomer; these prepolymers areendcapped with polymerizable ethylenically unsaturated radicals, such asHEMA reacted with isocyanate. These prepolymers may be copolymerizedwith a hydrophilic comonomer to form a silicone hydrogel copolymer thatis useful as a contact lens material or other biomedical deviceapplications. The preferred prepolymers of U.S. Pat. No. 5,034,461 arecomposed of soft polysiloxane segments (represented by A in the patentformulae) and strong hard segments (represented by *D*G*D* in the patentformulae), and are endcapped with polymerizable ethylenicallyunsaturated radicals.

The polysiloxane-containing prepolymers of this invention comprise morepolar urethane or urea linkages per polysiloxane molecular weight, incomparison with U.S. Pat. No. 4,136,250 or U.S. Pat. No. 4,605,712, andthe polysiloxane soft segment are linked to polymerizable groups thougha diisocyanate which provides two urethane/urea linkages instead of oneurethane/urea linkage in the case of U.S. Pat. No. 4,605,712, and arethus and are more compatible with hydrophilic monomers.

The polysiloxane-containing prepolymers of this invention compriserelatively weaker hard segments than the preferred prepolymers in U.S.Pat. No. 5,034,461. It has been found that this leads to severaladvantages. First, the present prepolymers tend to have a lowerviscosity at room temperature; in fact they are fluid, making themeasier to process in casting biomedical devices as compared toprepolymers with only strong hard segments such as those disclosed inU.S. Pat. No. 5,034,461. Second, this arrangement permits forming aprepolymer of higher silicone content, thereby permitting the formationof copolymers with higher oxygen permeabilities as compared toprepolymers disclosed in U.S. Pat. Nos. 4,136,250 or 4,605,712. In theprepolymers disclosed in these patents, the use of higher amounts ofpolysiloxane often leads to incompatibility when mixing monomer mixturesfor casting. Third, in some cases, copolymers offering the higher oxygenpermeabilities can be obtained without high modulus.

SUMMARY OF THE INVENTION

This invention provides a polysiloxane prepolymer that is useful forforming biomedical devices. The prepolymers are represented by thegeneral formula:M(*Dii*PS)_(x)*Dii*M  (I)wherein:

each M is independently a polymerizable ethylenically unsaturatedradical;

each Dii is independently a diradical residue of a diisocyanate;

each PS is independently a diradical residue of a polysiloxane-diol or-diamine;

each * is independently —NH—CO—NH—, —NH—COO— or —OCO—NH—; and

x is at least 2.

This invention further provides a copolymer that is the polymerizationproduct of a monomeric mixture comprising the prepolymer and acomonomer. One preferred comonomer is a hydrophilic monomer, and anotherpreferred comonomer is a monofunctional silicone-containing monomer.Preferred copolymers are hydrogels, that are the hydrated polymerizationproduct of a monomeric mixture comprising the prepolymer and ahydrophilic comonomer. Especially preferred are hydrogel copolymershaving a water content of at least 20 weight percent, a modulus nogreater than 100 g/mm2, and/or an oxygen permeability of at least 100barrers.

This invention further provides a biomedical device comprised of thecopolymer, especially an ophthalmic device such as a contact lens or anintraocular lens.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

The prepolymers of this invention are represented by the formula:M(*Dii*PS)_(x)*Dii*M  (I)wherein:

each M is independently a polymerizable ethylenically unsaturatedradical;

each Dii is independently a diradical residue of a diisocyanate;

each PS is independently a diradical residue of a polysiloxane-diol or apolysiloxane-diamine;

each * is independently —NH—CO—NH—, —NH—COO— or —OCO—NH—; and

x is at least 2.

Generally, the *Dii*PS blocks of formula (I) may be characterized ascomposed of relatively weak hard segments (represented by *Dii*) andsoft segments (represented by PS).

The prepolymers include polysiloxane-containing soft segments,represented by PS in formula (I). More particularly, thispolysiloxane-containing segment is derived from polysiloxanes endcappedwith hydroxyl or amino radicals:

wherein each A is a hydroxyl or amino radical;

each R is independently selected from an alkylene group having 1 to 10carbon atoms wherein the carbon atoms may include ether, urethane orureido linkages therebetween;

each R′ is independently selected from hydrogen, monovalent hydrocarbonradicals or halogen substituted monovalent hydrocarbon radicals whereinthe hydrocarbon radicals have 1 to 20 carbon atoms which may includeether linkages therebetween, and

a is at least 1.

Preferred R radicals are alkylene optionally substituted with etherradicals. Preferred R′ radicals include: alkyl groups, phenyl groups,fluoro-substituted alkyl groups and alkenyl groups, optionallysubstituted ether groups. Especially preferred R′ radicals include:alkyl, such as methyl; or fluoroalkyl optionally including etherlinkages, such as —CH2-CH2-CH2-O—CH2- (CF2)z-H where z is 1 to 6.

Preferably, a is about 10 to about 100, more preferably about 15 toabout 60. The Mn of PS ranges from 1000 to 8000, more preferably 2000 to6000.

Various polysiloxane-diols and polysiloxane-diamines are commerciallyavailable. Additionally, representative syntheses of polysiloxanes areprovided in the Examples.

The aforementioned polysiloxane-containing segments are linked viadiisocyanates that react with hydroxyl- or amino-functionality of thepolysiloxane-containing segments. Generally, any diisocyanate may beemployed. These diisocyanates may be aliphatic or aromatic, and includealkyl, alkyl cycloalkyl, cycloalkyl, alkyl aromatic and aromaticdiisocyanates preferably having 6 to 30 carbon atoms in the aliphatic oraromatic moiety. Specific examples include isophorone diisocyanate,hexamethylene-1,6- diisocyanate, 4,4′-dicyclohexylmethane diisocyanate,toluene diisocyanate, 4,4′-diphenyl diisocyanate, 4,4′-diphenylmethanediisocyanate, p-phenylene diisocyanate, 1,4-phenylene 4,4′-diphenyldiisocyanate, 1,3-bis-(4,4′-isocyanto methyl) cyclohexane, andcyclohexane diisocyanate.

In formula (I), x is at least two, more preferably at least three.

The prepolymers are endcapped at both ends with a polymerizableethylenically unsaturated radical, represented by M in formula (I).Representative M radicals may be represented by the formula:

wherein:

R₂₃ is hydrogen or methyl;

each R₂₄ is hydrogen, an alkyl radical having 1 to 6 carbon atoms, or a—CO —Y—R₂₆ radical

wherein Y is —0, —S— or —NH—;

R₂₅ is a divalent alkylene radical having 1 to 10 carbon atoms;

R₂₆ is an alkyl radical having 1 to 12 carbon atoms;

Q denotes —CO—, —OCO— or —COO—;

X denotes —0— or —NH—;

Ar denotes an aromatic radical having 6 to 30 carbon atoms; b is 0 to 6;c is 0 or 1; d is 0 or 1; and e is 0 or 1.

Suitable endcapping precursors, for forming the M radicals, include:hydroxy-terminated (meth)acrylates, such as 2-hydroxyethylmethacrylate,2-hydroxyethylacrylate, and 3-hydroxypropylmethacrylate; andamino-terminated (meth)acrylates, such as t-butylaminoethylmethacrylateand aminoethylmethacrylate; and (meth)acrylic acid. (As used herein, theterm “(meth)” denotes an optional methyl substituent. Thus, terms suchas “(meth)acrylate” denotes either methacrylate or acrylate, and“(meth)acrylic acid” denotes either methacrylic acid or acrylic acid.)

A representative reaction scheme for forming the prepolymers is asfollows. First, a diisocyanate is reacted with the polysiloxane-diol.(n+1)OCN-Dii-NCO+nHO—PS—OH→OCN-(Dii*PS)x*Dii-NCO

In this scheme, * designates a urethane radical —NH—COO— or —OCO—NH—.Generally, this reaction is conducted in the presence of a catalyst,such as dibutyl tin dilaurate and in a solvent, such as methylenechloride, and under reflux.

Finally, this product is endcapped with the polymerizable ethylenicallyunsaturated radical.OCN-(Dii*PS)_(n)*Dii-NCO+2M-OH→M(*Dii*PS)_(n)*Dii*M

In the above reaction scheme, the reaction of the polysiloxane-diol withthe diisocyanate yields urethane radicals (—NH—COO— or —OCO—NH—).Alternatively, the reaction of poly-siloxane-diamines with diisocyanateswould yield urea radicals (NH—CO—NH—). Other methods for formingurethane or urea polymers are known in the art, and representativesyntheses are illustrated in the Examples.

The copolymers of this invention are formed by copolymerizing theprepolymers of this invention with one or more comonomers. Since theprepolymers are endcapped with polymerizable ethylenically unsaturatedradicals, they are polymerizable by free radical polymerization. Themonomeric mixtures employed in the invention include conventionallens-forming or device-forming monomers. (As used herein, the term“monomer” or “monomeric” and like terms denote relatively low molecularweight compounds that are polymerizable by free radical polymerization,as well as higher molecular weight compounds also referred to as“prepolymers”, “macromonomers”, and related terms.) For copolymers, thesubject prepolymers are included in the monomer mixture at 5 to 95weight percent, preferably 20 to 70 weight percent.

A hydrophilic comonomer may be included in the initial monomeric mixturecontaining the subject prepolymer, for example, if it is desired toobtain a more hydrophilic copolymer or to form a hydrogel copolymer.Representative hydrophilic comonomers include: unsaturated carboxylicacids, such as methacrylic and acrylic acids; (meth)acrylic substitutedalcohols, such as 2-hydroxyethylmethacrylate, 2-hydroxyethylacrylate andglyceryl methacrylate; vinyl lactams, such as N-vinyl pyrrolidone; and(meth)acrylamides, such as methacrylamide and N,N-dimethylacrylamide. Ahydrogel is a crosslinked polymeric system that can absorb and retainwater in an equilibrium state. For hydrogel copolymers, at least onehydrophilic monomer is included in the monomer mixture at 20 to 60weight percent, preferably 25 to 50 weight percent.

Another class of lens-forming or device-forming monomers issilicone-containing monomers. In other words, anothersilicone-containing comonomer, in addition to the subject prepolymer,may be included in the initial monomeric mixture, for example, if it isdesired to obtain a copolymer with higher oxygen permeability.

One suitable class of silicone containing monomers include known bulky,monofunctional polysiloxanylalkyl monomers represented by Formula (VI):

X denotes —COO—, —CONR⁴—, —OCOO—, or —OCONR⁴— where each where R⁴ is Hor lower alkyl; R³ denotes hydrogen or methyl; h is 1 to 10; and each R²independently denotes a lower alkyl or halogenated alkyl radical, aphenyl radical or a radical of the formula—Si(R⁵)₃wherein each R⁵ is independently a lower alkyl radical or a phenylradical. Such bulky monomers specifically include methacryloxypropyltris(trimethylsiloxy)silane (TRIS), pentamethyldisiloxanylmethylmethacrylate, tris(trimethylsiloxy) methacryloxy propylsilane,methyldi(trimethylsiloxy)methacryloxymethyl silane,3-[tris(trimethylsiloxy)silyl] propyl vinyl carbamate, and3-[tris(trimethylsiloxy)silyl] propyl vinyl carbonate.

Various difunctional and multifunctional silicone-containing monomersare known in the art and may be used as a comonomer if desired. Themonomer mixtures may include the silicone monomer, in addition to thesubject prepolymers, at 0 to 50 weight percent, preferably 5 to 30weight percent when present.

In the case of silicone hydrogels, the monomer mixture includes acrosslinking monomer (a crosslinking monomer being defined as a monomerhaving multiple polymerizable functionalities). Since the subjectprepolymers are endcapped at both ends with a polymerizable radical, theprepolymers will function as a crosslinker. Optionally, a supplementalcrosslinking monomer may be added to the initial monomeric mixture.Representative crosslinking monomers include: divinylbenzene, allylmethacrylate, ethyleneglycol dimethacrylate, tetraethyleneglycoldimethacrylate, polyethyleneglycol dimethacrylate, vinyl carbonatederivatives of the glycol dimethacrylates, and 1-ethylene methacrylate,2-vinylcarbonate. When a supplemental crosslinking agent is employed,this monomeric material may be included in the monomer mixture at 0.1 to20 weight percent, more preferably at 0.2 to 10 weight percent.

In the case of intraocular lenses, the monomer mixtures may furtherinclude a monomer for increasing the refractive index of the resultantcopolymer. Examples of such monomers are aromatic (meth) acrylates, suchas phenyl (meth)acrylate, phenylethyl (meth)acrylate and benzyl(meth)acrylate.

An organic diluent may be included in the initial monomeric mixture. Asused herein, the term “organic diluent” encompasses organic compoundsthat are substantially unreactive with the components in the initialmixture, and are often used to minimize incompatibility of the monomericcomponents in this mixture. Representative organic diluents include:monohydric alcohols, such as C₂-C₁₀ monohydric alcohols; diols such asethylene glycol; polyols such as glycerin; ethers such as diethyleneglycol monoethyl ether; ketones such as methyl ethyl ketone; esters suchas methyl heptanoate; and hydrocarbons such as toluene.

In forming lenses or other biomedical devices, the monomeric mixturesmay be charged to a mold, and then subjected to heat and/or lightradiation, such as UV radiation, to effect curing, or free radicalpolymerization, of the monomer mixture in the mold. Various processesare known for curing a monomeric mixture in the production of contactlenses or other biomedical devices, including spincasting and staticcasting. Spincasting methods involve charging the monomer mixture to amold, and spinning the mold in a controlled manner while exposing themonomer mixture to light. Static casting methods involve charging themonomer mixture between two mold sections forming a mold cavityproviding a desired article shape, and curing the monomer mixture byexposure to heat and/or light. In the case of contact lenses, one moldsection is shaped to form the anterior lens surface and the other moldsection is shaped to form the posterior lens surface. If desired, curingof the monomeric mixture in the mold may be followed by a machiningoperation in order to provide a contact lens or article having a desiredfinal configuration. Such methods are described in U.S. Pat. Nos.3,408,429, 3,660,545, 4,113,224, 4,197,266, 5,271,875, and 5,260,000,the disclosures of which are incorporated herein by reference.Additionally, the monomer mixtures may be cast in the shape of rods orbuttons, which are then lathe cut into a desired shape, for example,into a lens-shaped article.

One preferred application of the subject prepolymers is hydrogel contactlenses. For contact lens applications, it is preferred that the hydrogelcopolymer, when fully hydrated, has a water content of at least 20weight percent, as measured gravimetrically.

Also, in some cases, it is preferred that the hydrogel copolymer has atensile modulus no greater than 100 g/mm². Modulus may be measured withan Instron (Model 4502) instrument according to ASTM D-1708a, where thehydrogel copolymer film sample is immersed in borate buffered saline. Anappropriate size of the film sample is gauge length 22 mm and width 4.75mm, where the sample further has ends forming a dogbone shape toaccommodate gripping of the sample with clamps of the Instroninstrument, and thickness of 200±50 microns.

It is preferred that the hydrogel copolymer has an oxygen permeabilityof at least 100 barrers, more preferably, at least 150 barrers. Oxygenpermeability (also referred to as Dk) is determined by the followingprocedure. The oxygen permeability of silicone hydrogels are measured bythe polarographic method (ANSI Z80.20-1998) using an O2 PermeometerModel 201T instrument (Createch, Albany, Calif. USA) having a probecontaining a central, circular gold cathode at its end and a silveranode insulated from the cathode. Measurements are taken only onpre-inspected pinhole-free, flat silicone hydrogel film samples of threedifferent center thicknesses ranging from 150 to 600 microns. Centerthickness measurements of the film samples may be measured using aRehder ET-1 electronic thickness gauge. Generally, the film samples havethe shape of a circular disk. Measurements are taken with the filmsample and probe immersed in a bath containing circulating phosphatebuffered saline (PBS) equilibrated at 35° C.+/−0.2°. Prior to immersingthe probe and film sample in the PBS bath, the film sample is placed andcentered on the cathode premoistened with the equilibrated PBS, ensuringno air bubbles or excess PBS exists between the cathode and the filmsample, and the film sample is then secured to the probe with a mountingcap, with the cathode portion of the probe contacting only the filmsample. For silicone hydrogel films, it is frequently useful to employ aTeflon polymer membrane, e.g., having a circular disk shape, between theprobe cathode and the film sample. In such cases, the Teflon membrane isfirst placed on the pre-moistened cathode, and then the film sample isplaced on the Teflon membrane, ensuring no air bubbles or excess PBSexists beneath the Teflon membrane or film sample. Once measurements arecollected, only data with correlation coefficient value (R²) of 0.97 orhigher should be entered into the calculation of Dk value. At least twoDk measurements per thickness, and meeting R² value, are obtained. Usingknown regression analyses, oxygen permeability (Dk) is calculated fromthe film samples having at least three different thicknesses. Any filmsamples hydrated with solutions other than PBS are first soaked inpurified water and allowed to equilibrate for at least 24 hours, andthen soaked in PHB and allowed to equilibrate for at least 12 hours. Theinstruments are regularly cleaned and regularly calibrated using RGPstandards. Upper and lower limits are established by calculating a+/−8.8% of the Repository values established by William J. Benjamin, etal., The Oxygen Permeability of Reference Materials, Optom Vis Sci 7(12s): 95 (1997), the disclosure of which is incorporated herein in itsentirety:

Material Name Repository Values Lower Limit Upper Limit Fluoroperm 3026.2 24 29 Menicon EX 62.4 56 66 Quantum II 92.9 85 101

The following Examples illustrate various preferred embodiments of theinvention.

EXAMPLE 1 Preparation of α,ω-bis(4-hydroxybutyl)polydimethylsiloxane (Mnabout 3600)

The following were charged to a 2-L, three-neck round-bottom flaskequipped with one reflux condenser: 51.26 grams of 1,3-bishydroxybutyltetramethyldisiloxane; 863 grams of dimethoxydimethylsilane; 126 gramsof distilled water; and 14.7 mL of concentrated hydrochloric acid. Themixture was heated at 60° C. for 1 hour. Methanol was then distilled offover a 5-hour period. Then, 279 ml distilled water and 279 mLconcentrated HCl were added, and the contents were refluxed at 100° C.for 3 hours. The crude product was then separated from the aqueouslayer. Then, 600 mL diethyl ether and 400 mL distilled water were added,and the solution was extracted twice with 400 mL sodium bicarbonatesolution (0.5%) and then with distilled water until the washing hadneutral pH. The product was then added slowly into a mixture ofmethanol/water (406 g/118 g). The bottom organic layer was separated,added with diethyl ether and dried with magnesium sulfate. Ether wasthen stripped under vacuum at room temperature and the residue wasfurther stripped under vacuum (0.07-mm torr) at 80° C. The final productwas recovered. The molecular weight (Mn) as determined by titration was3598.

EXAMPLE 2 Preparation of α,ω-polydimethylsiloxane prepolymer using PDMSof Example 1

A dry 3-neck, 500-mL round-bottom flask was connected to a nitrogeninlet tube and a reflux condenser. The following were added to the flaskall at once: isophorone diisocyanate (9.188 g, 41.333 mmol) (IPDI);α,ω-bis(4-hydroxybutyl)-polydimethylsiloxane from Example 1 (114.68 g,31.873 mmol) (PDMS); dibutyl tin dilaurate (0.327 g); and 180 mLmethylene chloride. The contents were refluxed. After overnight, theamount of isocyanate was determined to decrease to 22.0% by titration.The contents were cooled down to ambient temperature. 1,1′-bi-2-naphthol (0.0144 g) and 2-hydroxyethyl methacrylate (2.915 g, 22.399mmol) were then added and the contents were stirred at ambient untilisocyanate peak at 2267 cm⁻¹ disappeared from IR spectrum of theproduct. The solvent was then stripped under reduced pressure and theproduct was recovered (126 g). Theoretically, the prepolymer had 3blocks containing of PDMS (x about 3).

EXAMPLE 3 Preparation of α,ω-polydimethylsiloxane prepolymer using PDMSof Example 1

The general procedure of Example 2 is followed, except that the molarratio of PDMS to IPDI is 4:5, respectively. 149.6 g of prepolymer wasrecovered. Theoretically, the prepolymer had 4 blocks containing of PDMS(x about 4).

EXAMPLE 4 Preparation of α,ω-polydimethylsiloxane prepolymer using PDMSof Example 1

The general procedure of Example 2 is followed, except that the molarratio of PDMS to IPDI is 5:6, respectively. 159.9 g of prepolymer wasrecovered. Theoretically, the prepolymer had 5 blocks containing of PDMS(x about 5).

EXAMPLES 5-14

Copolymers

Monomer mixtures were made by mixing the following components, listed inTables 1 and 2 at amounts per weight: prepolymers of Examples 2, 3 and4; methacryloxypropyl tris(trimethylsiloxy)silane (TRIS);N,N-dimethylacrylamide (DMA); 2-hydroxy ethyl methacrylate (HEMA);N-vinyl pyrrolidone (NVP); and/or methacryloxyethyl vinylcarbonate(HemaVC). Additionally, each monomer mixture included:1,4-bis(2-methacrylamidoethylamino)anthraquinone as a tint (150 ppm);hexanol as a diluent (10 parts by weight); and Darocur™ UV initiator(Ciba Specialty Chemical, Ardsley N.Y.) (0.5 wt %).

The monomer mixtures were cast between silane-treated glass plates, andthen cured under UV light for 1 hour. Each monomer mixture was castbetween three sets of glass plates, each set of plates separated byTeflon™ polymer tapes of different thicknesses, such that three sets offilm samples were obtained for each monomer mixture, with filmthicknesses of about 200, 400 and 600 microns. The cured films were thenextracted with isopropanol overnight, followed by hydration in deionized(DI) water, boiled in DI water for 4 hours and then saturated in boratebuffered saline or phosphate buffered saline to give hydrogel films. Thewater content was measured gravimetrically. Mechanical tests wereconducted in borate buffered saline according to ASTM D-1708a, discussedabove. The oxygen permeabilities, reported in Dk (or barrer) units, weremeasured in phosphate buffered saline at 35° C., using acceptable filmswith three different thicknesses, as discussed above.

TABLE 1 Example 5 6 7 8 9 Prepolymer Ex 2 65 65 60 65 — Prepolymer Ex 3— — — — 65 Tris 10 10 15 10 10 DMA 15 12 12 25 25 NVP 10 10 10 — — Hema— 5 5 — — HemaVC 0.5 0.5 0.5 — — % Water 19.6 18.4 19.1 19.3 22.3 Dk(barrer) 224 300 224 219 257 Modulus (g/mm²) 187 180 143 152 102

TABLE 2 Example 10 11 12 13 14 Prepolymer Ex 3 65 60 — — — Prepolymer Ex4 — — 65 65 60 Tris 10 15 10 10 15 DMA 12 12 25 12 15 NVP 10 10 — 5 10Hema 5 5 — — 2 HemaVC 0.5 0.5 — 0.5 0.5 % Water ND ND 25.9 ND 23.9 Dk(barrer) ND ND 171 ND 159 Modulus (g/mm²) ND ND 85 ND 79

The monomer mixtures prepared in Examples 10, 11 and 13 were cloudy sono films were cast. As the prepolymer in these examples were less polar,this suggests that prepolymers of lower polarity are less compatiblewith hydrophilic monomers. All hydrogel films were optically clear.

Having thus described various preferred embodiment of the invention,those skilled in the art will appreciate that various modifications,additions, and changes may be made thereto without departing from thespirit and scope of the invention, as set forth in the following claims.

1. A hydrogel copolymer that is the hydrated polymerization product of amonomeric mixture comprising a prepolymer represented by the generalformula:M(*Dii*PS)_(x)*Dii*M  (I) wherein: each M is independently apolymerizable ethylenically unsaturated radical; each Dii isindependently a diradical residue of a diisocyanate; each PS isindependently a diradical residue of a polysiloxane-diol or apolysiloxane-diamine; each * is independently —NH—CO—NH—, —NH—COO— orOCO—NH—; and x is at least 2, and a hydrophilic comonomer, and whereinthe hydrogel copolymer has sufficient optical quality and an oxygenpermeability of at least 150 barrers.
 2. The hydrogel copolymer of claim1, wherein each Dii is a diradical residue of a diisocyanate selectedfrom the group consisting of isophorone diisocyanate,hexamethylene-1,6-diisocyanate, 4,4′-dicyclohexylmethane diisocyanate,toluene diisocyanate, 4,4′-diphenyl diisocyanate, 4,4′-diphenylmethanediisocyanate, p-phenylene diisocyanate, 1,4-phenylene 4,4′-diphenyldiisocyanate, 1,3-bis-(4,4′-isocyanto methyl) cyclohexane, andcyclohexane diisocyanate.
 3. The hydrogel copolymer of claim 1, whereinMn of PS ranges from 1000 to
 8000. 4. The hydrogel copolymer of claim 1,wherein x is at least
 3. 5. The hydrogel copolymer of claim 1, whereineach M is independently a polymerizable ethylenically unsaturatedradical of the formula:

wherein: R₂₃ is hydrogen or methyl; each R₂₄ is hydrogen, an alkylradical having 1 to 6 carbon atoms, or a —CO—Y—R₂₆ radical wherein Y is—O—, —S— or —NH—; R₂₅ is a divalent alkylene radical having 1 to 10carbon atoms; R₂₆ is a alkyl radical having 1 to 12 carbon atoms; Q is—CO—, —OCO— or —COO—; X is —O— or —NH—; Ar is an aromatic radical having6 to 30 carbon atoms; b is 0 to 6; c is 0 or 1; d is 0 or 1; and e is 0or
 1. 6. The hydrogel copolymer of claim 1, wherein: each M is2-ethylenemethacrylate; each Dii is the diradical residue of isophoronediisocyanate; each PS is a diradical residue of apolydimethylsiloxane-diol having Mn of at least 2000 to 3600; and each *is —NH—COO— or —OCO—NH—.
 7. The hydrogel copolymer of claim 1, whereinthe hydrophilic monomer is selected from the group consisting of:unsaturated carboxylic acids; (meth)acrylic substituted alcohols; vinyllactams; and (meth)acrylamides.
 8. The hydrogel copolymer of claim 7,wherein the hydrophilic monomer is selected from the group consistingof: methacrylic acid; acrylic acid; 2-hydroxyethylmethacrylate; glycerylmethacrylate; N-vinyl pyrrolidone; methacrylamide; andN,N-dimethylacrylamide.
 9. The hydrogel copolymer of claim 1, whereinthe monomeric mixture further comprises a monofunctionalsilicone-containing monomer.
 10. The hydrogel copolymer of claim 9,wherein the monomeric mixture further comprises methacryloxypropyltris(trimethylsiloxy)silane.
 11. The hydrogel copolymer of claim 1,having a water content of at least 20 weight percent.
 12. The hydrogelcopolymer of claim 1, having a modulus no greater than 100 g/mm². 13.The hydrogel copolymer of claim 1, having a water content of at least 20weight percent, and a modulus no greater than 100 g/mm².
 14. Abiomedical device comprising a hydrogel copolymer of claim
 1. 15. Thehydrogel copolymer of claim 1, wherein x is at least 2 to about
 5. 16.The hydrogel copolymer of claim 1 wherein each PS is a diradical residueof a polydimethylsiloxane-diol having Mn of at least 2000 to
 3600. 17.An ophthalmic device comprising a hydrogel copolymer that is thehydrated polymerization product of a monomeric mixture comprising aprepolymer represented by the general formula:M(*Dii*PS)_(x)*Dii*M  (I) wherein: each M is independently apolymerizable ethylenically unsaturated radical; each Dii isindependently a diradical residue of a diisocyanate; each PS isindependently a diradical residue of a polysiloxane-diol or apolysiloxane-diamine; each * is independently —NH—CO—NH—, —NH—COO— orOCO—NH—; and x is at least 2, and a hydrophilic comonomer, and whereinthe hydrogel copolymer has sufficient optical quality and an oxygenpermeability of at least 150 barrers, wherein the ophthalmic device is acontact lens or an intraocular lens.
 18. The ophthalmic device of claim17, wherein x is at least 2 to about
 5. 19. The ophthalmic device ofclaim 17, wherein the monomeric mixture further comprises amonofunctional silicone-containing monomer.
 20. The ophthalmic device ofclaim 17, wherein each PS is a diradical residue of apolydimethylsiloxane-diol having Mn of at least 2000 to
 3600. 21. Theophthalmic device of claim 17, having a water content of at least 20weight percent, a modulus no greater than 100 g/mm².
 22. A contact lenscomprising a hydrogel copolymer that is the hydrated polymerizationproduct of a monomeric mixture comprising a prepolymer represented bythe general formula:M(*Dii*PS)_(x)*Dii*M  (I) wherein: each M is independently apolymerizable ethylenically unsaturated radical; each Dii isindependently a diradical residue of a diisocyanate; each PS is adiradical residue of a polydimethylsiloxane-diol having Mn of at least2000 to 3600; each * is independently —NH—CO—NH—, —NH—COO— or OCO—NH—;and x is at least 2, and a hydrophilic comonomer, and wherein thehydrogel copolymer has sufficient optical quality and an oxygenpermeability of at least 100 barrers.
 23. The contact lens of claim 22having a water content of at least 20 weight percent, and a modulus nogreater than 100 g/mm².
 24. The contact lens of claim 22 wherein x is atleast 2 to 5.